Simultaneous multi-slice recording of magnetic resonance data

ABSTRACT

A method for the simultaneous recording of magnetic resonance data relating to an examination subject from at least two different slices by a magnetic resonance sequence, wherein an excitation period of the magnetic resonance sequence that includes at least one sub-section that acts on only one of the slices, and that contains at least one high frequency pulse is used, wherein, to correct the main magnetic field inhomogeneities of the first order, for each slice affected by a sub-section, a correction parameter that modifies the gradient pulses that are to be emitted is determined, taking into account at least one main magnetic field map that describes the spatial distribution of the main magnetic field and a slice position of the affected slice and is applied in the emission of gradient pulses for the respective slice in the sub-section.

The application claims the benefit of German Patent Application No. DE10 2017 208 746.3, filed May 23, 2017, which is hereby incorporated byreference in its entirety.

TECHNICAL FIELD

The disclosure relates to a method for the simultaneous recording ofmagnetic resonance data relating to an examination subject from at leasttwo different slices by a magnetic resonance sequence, wherein anexcitation period of the magnetic resonance sequence including at leastone sub-section that acts on only one of the slices, containing at leastone high frequency pulse, is used. The disclosure additionally relatesto a magnetic resonance apparatus, a computer program, and anelectronically readable data carrier.

BACKGROUND

Magnetic resonance (MR) imaging is a known technique with which imagesof the inside of an examination subject may be generated, e.g., of apatient in medical imaging. For this purpose, the examination subject ispositioned in a magnetic resonance apparatus in a comparatively strongstatic, homogeneous main magnetic field, also known as the B₀-Feld, withfield strengths of 0.2 tesla to 7 tesla and more, such that the nuclearspins thereof are orientated along the main magnetic field. To triggernuclear magnetic resonances, high frequency excitation pulses (alsoknown as RF-pulses) are radiated into the examination subject. Thenuclear magnetic resonances that are triggered are measured as what isknown as k-space data. On the basis thereof, MR images are reconstructedor spectroscopy data is acquired. For the spatial encoding of themagnetic resonance data, rapidly switched magnetic gradient fields aresuperimposed on the main magnetic field. The magnetic resonance datathat has been recorded is digitalized and stored as complex numericalvalues in a k-space matrix. From the k-space matrix that is occupied byvalues, a relevant MR image may be reconstructed, for example, by amulti-dimensional Fourier transform.

The desire for faster and faster magnetic resonance images in theclinical environment is currently leading to a renaissance of methods inwhich magnetic resonance data from different volume regions of theexamination subject, in particular therefore from different slices in astack of slices, may be recorded simultaneously. These methods may becharacterized in that, at least during a part of the measurement,transversal magnetization of at least two slices is used at the sametime for the imaging process (“slice-multiplexing”; e.g., known in assimultaneous multi-slice (SMS) imaging). In conventional multi-sliceimaging, the signal from at least two slices is recorded consecutivelyor alternately, that is, completely independent of each other, with anaccordingly longer measurement time.

Known methods for this purpose are “Hadamard-coding”, methods withsimultaneous echo-refocusing, methods with broadband data recording oreven methods that use parallel imaging in the slice direction. Thelatter methods also include, for example, the blipped ControlledAliasing in Parallel Imaging (CAIPI) technique, as described bySetsompop et al. in “Blipped-Controlled Aliasing in Parallel Imaging forSimultaneous Multislice Echo Planar Imaging with Reduced g-FactorPenalty”, Magnetic Resonance in Medicine 67, 2012, p. 1210-1224.

U.S. Patent Application Publication No. 2016/0313433 A1 and U.S. PatentApplication Publication No. 2015/0115958 A1 disclose methods forsimultaneous multi-slice measurement.

In such slice-multiplexing methods, what is known as a multiband highfrequency pulse is used in order to excite or otherwise manipulate twoor a plurality of slices at the same time, for example, to refocus orsaturate them. Such a multiband high frequency pulse is, for example, amultiplex of individual single-slice high frequency pulses, which wouldbe used for the manipulation of the slices that are to be manipulated atthe same time. In order to be able to separate the resulting magneticresonance signals from the various slices, each of the individual highfrequency pulses is imprinted with a different phase, (e.g., prior tomultiplexing), by adding a linear phase shift, for example, as a resultof which the slices are shifted with respect to one another in thelocation domain. Through multiplexing, one obtains, for example, a basicband-modulated multiband high frequency pulse by adding the shapes ofthe pulses in the individual single-slice high frequency pulses.

As described, for example, in the article by Setsompop et al. citedabove, the g-factor-related disadvantages may be reduced by shiftsbetween the slices, by using gradient blips for instance or bymodulating the phases of the individual high frequency pulses. Aslikewise disclosed in the cited article by Setsompop et al., the signalsfrom the slices that have been excited or otherwise manipulated at thesame time may first be combined like signals from only one slice inorder for them to then be separated in the subsequent processing by aslice GeneRalized Auto-calibrating Partial Parallel Acquisition (GRAPPA)method.

In the prior art, it has also already been suggested in the context ofslice-multiplexing to excite or manipulate in a different way differentslices that are meant to be scanned at the same time, such thatdifferent contrasts emerge. In this context, U.S. Patent ApplicationPublication No. 2017/0108567 A1 proposes a method for simultaneousmulti-contrast recording in SMS imaging, in which with “inversionrecovery”, (IR) images may be acquired at the same time as non-IRimages, by applying a single band inversion pulse to only one of theslices.

Likewise, with regard to saturation of certain types of spin, the Larmorfrequencies of which differ due to a chemical shift, there are alreadyrelevant suggestions in existence. The types of spins possiblyconsidered are spins of fat-bound protons (“fat spins”) and spins ofwater-bound protons (“water spins”). A traditional measure adopted inthis context is “fat saturation”. In this context, the subsequentlypublished U.S. Patent Application Publication No. 2018/0024214 disclosescombining a binomial pulse for water excitation for a slice with aconventional excitation pulse for the other slice in order to acquireone slice with and one slice without fat saturation. The subsequentlypublished U.S. Patent Application Publication No. 2018/0074146 proposesa method of spatial fat-suppression in multi-contrast SMS imaging, inwhich a pulse sequence acting on only one slice with a binomial pulsefor fat excitation and a dephasing gradient are applied upstream of thefurther high frequency pulses in order to achieve fat saturation in saidslice. The problem here is that the fat saturation may be inadequate inregions with strong B0 distortions. This is because, in those regions,the spins experience stronger or weaker dephasing because the gradientmoment that is in fact acting on the spins is generated by thecombination of the bipolar gradients and of the deviations in the mainmagnetic field.

Methods based on magnetic resonance, such as tomographic imaging (e.g.,magnetic resonance tomography (MRT)) and spectroscopy (e.g., magneticresonance spectroscopy (MRS)), may need “benign” physical environmentalconditions in order to guarantee an optimum quality of the dataacquired. For example, this applies to at least one of the criteriaincluding spatial homogeneity, temporal stability, and the absoluteaccuracy of the magnetic fields relevant to MR methods (B₀, thestationary main magnetic field, and B₁, the high frequency magneticfield).

Already known methods with which deviations from ideal environmentalconditions may be at least partly compensated for include bothsystem-specific adjustments that seek to correct the given parameters ofthe magnetic resonance apparatus used, such as for example, eddycurrent-induced dynamic field distortions or likewise gradientsensitivities, and also examination subject-specific adjustments thatattempt to compensate for the changes caused by putting the examinationsubject, (e.g., a patient), into the measurement volume of the magneticresonance apparatus, such as susceptibility-related static fielddistortions or spatial variations in the high frequency field, forinstance. To compensate for non-ideal environmental conditions, theaffected parameters of the magnetic resonance sequences may be adjusted.In particular, parameters that come into consideration here are therespective central excitation frequency (for example, for an improvedfat-suppression and/or a reduced EPI image shift), shimming of the B0field in the first order (for example, for more homogeneousfat-suppression and/or an improved signal-noise ratio (SNR)), arespective electric voltage of each of the high frequency transmissionunits (for example, for an improved SNR) and/or B1-shimming (forexample, for a more homogeneous SNR). Such examination subject-specificparameters may be derived, for example, from B0 field maps or B1 fieldmaps that have been drawn beforehand.

An adjustment of these recording parameters was first described only forcoherent volumes and not, for example, for unconnected slices such asthose that are excited or manipulated at the same time inslice-multiplexing. Because the slices to be manipulated at the sametime in the slice-multiplexing method are normally arranged as far apartfrom each other as possible in order to make it easier to separate theslices into signals later, with these methods, an optimization volume inwhich deviations in the environmental conditions may be correctedtherefore includes either the entire stack of slices or at least theenvelope of the slices that are to be manipulated at the same time. Theparameters included therein are therefore only adjusted on average forthe optimization volume and may even be randomly unsuitable for theslices that are actually affected. In particular with measurements onregions of the examination subject with spatially rapidly varyingenvironmental conditions, such as in the region of the patient's head,such adjustments of recording parameters averaged out over fairly largevolumes may even lead to the result worsening.

The subsequently published German Patent Application Publication No. DE10 2016 214 088.4, which has been incorporated in its entirety into thedisclosure content of the present description, discloses in this contexta method for the slice-specific adjustment of RF pulses in recordings ofmagnetic resonance data relating to an examination subject with the aidof a slice-multiplexing method in which, for each slice that is to bescanned at the same time, single-slice RF pulse parameters aredetermined on the basis of the slice position, the single-slice RF pulseparameters are corrected on the basis of at least one examinationsubject-specific parameter map (e.g., B0 map and/or B1 map), which ineach case shows the spatial distribution of one system parameter in theexamination subject and of the slice position are corrected and amulti-band RF pulse for the manipulation of the slices to be scanned atthe same time is generated on the basis of the corrected single-slice RFpulse parameters. Here, parameters to be adjusted relate to thecentral-excitation frequency, an amplitude-scaling factor (e.g.,transmitter voltage) and/or B1 shim parameters. A correction relating toterms of the first order in the main magnetic field is not possible bythe high frequency pulses, so that only the aforementioned averagedcorrection that considers all the slices measured together is suggestedthere.

This is particularly problematic with regard to different contrasts andthe approaches to fat saturation described in the aforementioned becauseit has transpired that B0 field deviations of the first order are themain reason for a non-homogeneous fat saturation and other inhomogeneouscontrasts.

SUMMARY AND DESCRIPTION

The scope of the present disclosure is defined solely by the appendedclaims and is not affected to any degree by the statements within thissummary. The present embodiments may obviate one or more of thedrawbacks or limitations in the related art.

The disclosure addresses the problem of providing an option forimproving the quality of the magnetic resonance data in multi-contrastslice multiplexing imaging.

In a method, provision is therefore made to correct main magnetic fieldinhomogeneities of the first order for each slice affected by asub-section such that a correction parameter that modifies the gradientpulses that are to be emitted is determined, taking into account atleast one main magnetic field map that describes the spatialdistribution of the main magnetic field and a slice position of theaffected slice and that said parameter is applied in the emission ofgradient pulses for the respective slice in the sub-section.

Use is made of the fact that sub-sections of the excitation module ofthe magnetic resonance sequence completed in the excitation periodrelate only to specific slices and therefore slice-specific correctionsrelating to the deviations of first order in the main magnetic field maybe carried out, which corrections would not be possible and thereforehave not been considered until now in the prior art in the event thatall the slices that are to be acquired are influenced simultaneously. Inthis way, the present disclosure therefore specifically discloses aB0-gradient shimming method of the first order for an improved imagedata quality in general and an improved contrast homogeneity, (e.g., afat saturation homogeneity), which method may be applied tomulti-contrast SMS imaging. With regard to the selective excitationand/or suppression of specific types of spin in only one of the slicesthat are to be scanned simultaneously, use is made of the fact that thesuppression- or excitation modules (e.g., pulse sequences) at leastpartly target only one single, specific slice. Altogether, it is pointedout that the term “excitation period” is to be interpreted broadly andis also intended to include the emission of high frequency pulses thathave a manipulative effect on at least one slice, for example,refocusing pulses and suchlike. In particular, the sub-section may alsocover relaxation periods in only one slice.

It has transpired that, through the method, a clear increase in thequality of the magnetic resonance data recorded in this way is providedbecause the correction ensues directly in sensitive parts of themagnetic resonance sequence that until now had a negative effect if, forexample, they were subjected to an overall correction. Precisely withregard to selective excitation or selective suppression of types ofspin, for example, of fat spins and/or water spins, the homogeneity ofthe selective excitation/suppression may be improved, which is crucialfor the overall quality of the multi-contrast magnetic resonance data.

In concrete terms, provision may be made for a gradient offset that isto be applied as a correction parameter to a slice selection gradient tobe determined. Basic options for B0 shimming of the first order byadjusting gradient pulses have already been described in the prior artand may also be used accordingly in the context of the presentdisclosure. What is particularly easy to implement is the use ofgradient offsets at least in the at least one slice selection direction.

It should be further mentioned at this point that, during an overallmulti-contrast SMS imaging procedure, a plurality of slice combinationsmay be recorded consecutively. Here the method provides a dynamicadjustment of the correction parameters depending on the slices that arecurrently to be recorded/are affected in order to allow an optimumdynamic readjustment/correction.

A further development makes provision such that, for high frequencypulses and/or sub-pulses acting on a plurality of slices includingremaining sections of the excitation period, a correction parameter islikewise determined and applied jointly in each case for all theaffected slices. While it is possible therefore to carry out nocorrections at all in the remaining sections with regard to deviationsof the first order in the main magnetic field, it may be useful in atleast some of the potential scenarios to jointly consider a plurality ofslices affected and therefore manipulated at the same time and tolikewise find a correction solution in this case too, which solution mayrelate, for example, to the entire stack of slices, but also to a volumethat envelops the slices affected by the relevant residual section. Theremaining sections may be understood as multi-band excitation modules ormanipulation modules, which indeed cannot be optimized in aslice-specific manner but may be used for the averaged correctionparameters, as is basically known in the prior art. All the same, it ispointed out that less of an improvement is expected here, (e.g., alsowith regard to a shimming of a selection module), according to which themain advantage is the more homogeneous contrasts, which are alreadyachieved, however, by the correction in the sub-sections.

In order to achieve a further improvement, provision may be made suchthat for each slice, single slice high frequency pulse parameters thatdescribe single slice pulses of the excitation period affecting saidslice are determined on the basis of the slice position and arecorrected taking into account the main magnetic field map and/or a highfrequency field map, which describes the spatial distribution of thehigh frequency field, and the respective slice position, wherein thehigh frequency pulses that are to be emitted in the excitation periodare determined on the basis of the corrected single-slice high frequencypulse parameters. Therefore, in addition to the slice-specificB0-shimming by gradient correction in the sub-sections that is provided,the slice-specific correction that is applicable over the entireexcitation period, as described in the subsequently published GermanPatent Application Publication No. DE 10 2016 214 088.4, mayadvantageously also be used. The description in that documentaccordingly likewise continues to be applicable accordingly within thecontext of the present disclosure. In particular therefore, a centralexcitation frequency and/or an amplitude scaling factor and/or a B1 shimparameter may be used as single-slice high frequency pulse parameters.Through this correction of the single-slice high frequency pulseparameters on the basis of at least one examination subject-specificmain magnetic field map (e.g., B0 map) and/or examinationsubject-specific high frequency field map (e.g., B1 map), thesingle-slice high frequency pulse parameters may be adjusted tocurrently prevalent environmental conditions. Through the generation ofmultiband high frequency pulses on the basis of the already correctedsingle slice high frequency pulse parameters, the resulting multibandhigh frequency pulses are themselves adjusted in a slice-specific mannerto the current environmental conditions, such that alreadyslice-specifically adjusted single-slice high frequency pulses may becombined by multiplexing into what are then likewise slice-specificallyadjusted multiband high frequency pulses, as a result of which a furtherquality improvement in the magnetic resonance data is achieved in eachcase in a slice-accurate manner, in particular with regard to thesignal-to-noise ratio, the homogeneity of the signal-to-noise ratio andalso the contrast homogeneity, in particular in fat-suppression. Togenerate the multiband high frequency pulse, corresponding single-slicehigh frequency pulses may be added together, and it is also conceivablefor a gradient moment-based Maxwell term correction method to be used.

It should be further mentioned at this point that it is not theintention in the present application to go into further detail about theselection of the slice positions of the slices that are to be scannedsimultaneously because a very wide range of options has already beendiscussed in the prior art, which of course may also be appliedaccordingly within the context of the present disclosure.

A further development makes provision such that, in the sub-section, apulse sequence serving to saturate or excite spins of a particular spintype in the affected slice is emitted, in particular including afrequency-selective binomial pulse and/or a subsequent dephasinggradient pulse. The procedure described here may therefore beparticularly advantageously applied to specific, slice-specificexcitation and/or suppression modules that may be emitted before furtherhigh frequency pulses that act on a plurality of slices. A suppressionmodule for a type of spin, (e.g., fat spins), may include a pulsesequence in which fat spins are first excited selectively in theaffected slice in order to then be specifically dephased by a dephasinggradient. For further detail, reference is made here to theaforementioned subsequently published U.S. Patent ApplicationPublication No. 2018/0074146. In the context of the present disclosure,such a suppression module is optimized with respect to the affectedspecific slice, taking into account the environmental conditions, andtherefore a particularly homogeneous suppression is achieved; the samemay of course apply with regard to a selective excitation module used asa pulse sequence.

Additionally, or alternatively, it is conceivable that at least onebinomial pulse that includes sub-pulses acting on only one slice is usedas a high frequency pulse, wherein the sub-pulses acting on only oneslice define the sub-section. Likewise, in a procedure described forexample, in the subsequently published U.S. Patent ApplicationPublication No. 2018/0024214, the disclosure may therefore be usefullyemployed to improve the quality of the magnetic resonance data. Forexample, such a combined binomial pulse may be used for the simultaneouswater excitation for a first slice and to excite both fat and water fora second slice. Specific sub-pulses of the binomial pulse are directedhere only at the first slice, where the excitation of fat spins is to besuppressed, such that for these sub-pulses, slice-specific correctionparameters may be used for the corresponding gradient pulses. Forsub-pulses that affect both or all the slices, the correction may beomitted, or as described above, an averaged correction parameter, (e.g.,gradient offset), may be applied. The majority of the period of time inwhich the phase evolution for fat spins and water spins occurs in thefirst slice is, however, covered by the slice-specific correction ofmain magnetic field inhomogeneities of the first order, such that aclear improvement in the quality of the fat saturation occurs.

In addition to the method, the present disclosure also relates to amagnetic resonance apparatus, including a control apparatus that isembodied to carry out the method disclosed herein. In particular,alongside sequence control units potentially provided for running amagnetic resonance sequence, the control apparatus may also include acorrection unit, in which the correction parameter may be determined asdescribed, and a corresponding dynamic readjustment or adjustment of themagnetic resonance sequence may ensue. A further correction unit may beused, as described, to implement the correction method disclosed inGerman Patent Application Publication No. DE 10 2016 214 088.4, whichsuppresses single-slice high frequency pulses. All the statements madewith reference to the method may likewise be applied to the magneticresonance apparatus, with which the advantages already referred to maytherefore likewise be achieved.

A computer program is, for example, able to be loaded directly into amemory of a control device of a magnetic resonance apparatus and hasprogramming mechanisms in order to implement the acts of the method whenthe computer program is run in the control apparatus of a magneticresonance apparatus, by a processor, for example. The computer programmay be stored on an electronically readable data carrier, whichtherefore includes electronically readable control data that is storedthereon, which includes at least one named computer program and areembodied such that, when the data carrier is used in a control apparatusof a magnetic resonance apparatus, the data may run the method. The datacarrier may be a non-transient data carrier, (e.g., a CD-ROM).

BRIEF DESCRIPTION OF THE DRAWINGS

Further advantages and details of the present disclosure will emergefrom the exemplary embodiments that are described below and from thedrawing, in which:

FIG. 1 depicts an example of a schematic flow diagram explaining SMSimaging.

FIG. 2 depicts an example of a basic sequence diagram to be used.

FIG. 3 depicts a sub-section of the excitation period according to FIG.2.

FIG. 4 depicts a section from a further sequence diagram to explain afurther example of a use.

FIG. 5 depicts an example of a magnetic resonance apparatus.

DETAILED DESCRIPTION

To explain the background to the present disclosure, FIG. 1 depicts aworkflow of a slice-multiplexing imaging procedure (e.g., SMS imagingprocedure) with a magnetic resonance apparatus. Here, at least twoslices 1, 2, 3 are first excited at the same time in an examinationsubject 4, in this case a patient's head, and the resulting magneticresonance signals are acquired simultaneously as magnetic resonance datafrom each of slices 1 to 3. The result of this act is a data set ink-space, which set includes magnetic resonance data from the pluralityof slices 1, 2, 3 superimposed one over the other. For acquisition, inact 5 the Blipped Controlled Aliasing in Parallel Imaging Results inHigher Acceleration (CAIPIRINHA) technique is used, as explained, forexample, in the article by Setsompop et al. referenced above.

The magnetic resonance data that has been recorded in this way isseparated into the various slices in acts 6 by a slice GRAPPA algorithm,it being possible to add further acts 7 onto the acts 6 for each ofslices 1, 2, 3 in order to apply an in-plane GRAPPA algorithm, if anin-plane acceleration is available at all. This results in magneticresonance images for the individual slices 1, 2, 3.

FIG. 2 depicts a sequence diagram for a magnetic resonance sequence formulti-contrast SMS imaging, in which the procedure that is explainedbelow may be used. The sequence diagram 2 clearly includes consecutivetime sections, that is, a fat saturation module 8 (e.g., fat saturationpulse sequence) that acts on a first slice and a conventional Turbo SpinEcho (TSE) module 9, which relates to all the slices 1, 2, 3 that are tobe scanned at the same time, the high frequency pulses of which 10, 11therefore act on all the slices 1, 2, 3 that are to be scanned at thesame time. The high frequency pulse 10 is a multiband excitation pulse,and the high frequency pulses 11 are multiband refocusing pulses.

FIG. 3 depicts parts of the saturation module 8 in closer detail, thatis, the high frequency pulse component (RS) and the slice detectiongradient component (G_(z)). It is clear that in the present case a 1-2-1binomial pulse 12 is used, which pulse includes three sub-pulses 13. Thegap between the sub-pulses 13 is selected as a function of the chemicalshift between fat spins and water spins as spin types such that only fatspins are excited by the binomial pulse 12 as a high frequency pulse,after the transversal magnetization of the water spins has been rotatedinto the opposite direction by the second sub-pulse 13 (2 a) andtherefore returns to zero again due to the final sub-pulse. Here, thebinomial pulse 12 acts only on one of the plurality of slices 1, 2, 3due to the slice selection gradient pulse 14.

Prior to emitting the gradient pulses 14, in the context of theexemplary embodiment of the method that is used here, a determination ofcorrection parameters to correct main field inhomogeneities of the firstorder has already been carried out for the slice, and indeed on thebasis of the known position of the affected slice, that is, based on theslice position, and a main magnetic field map (e.g., B0 map), which hasbeen acquired in an examination subject-specific manner and thereforedescribes the actual examination subject-specific environmentalconditions. In the present case, gradient offsets 15 to be applied tothe slice selection gradient G_(z) have been determined as correctionparameters. These are also applied accordingly, as depicted in FIG. 3,such that the main magnetic field inhomogeneities of the first order forthe affected slice may be corrected accordingly. The part of theexcitation period depicted in FIG. 3 may therefore be understood as asub-section 16, in which the high frequency pulses (e.g., the binomialpulse 12) act only on a single slice of all the slices 1, 2, 3 that areto be scanned at the same time.

For the remaining sections of the excitation period, therefore for theemission of the high frequency pulses 10, 11 (cf. FIG. 2), either nosuch correction is applied in the case of the gradient pulses or,however, an averaged correction is applied, which relates to a volumethat encompasses all the slices 1, 2, 3 that have been excited ormanipulated at the same time.

It should be further mentioned at this point that a continuous furtherslice-specific correction does exist, which relates to the highfrequency pulses 10, 11 and to the binomial pulse 12. This is because,for each slice, in the present exemplary embodiment, single-slice highfrequency pulse parameters that describe single-slice pulses of theexcitation period affecting said slice have been determined on the basisof the slice positions and have then been corrected, taking into accountthe aforementioned main magnetic field map and a high frequency fieldmap (e.g., B1 map) that describes the spatial distribution of the highfrequency field and also the respective slice position. The highfrequency pulses 10, 11, 12 that were actually to be emitted in theexcitation period have then been determined on the basis of thecorrected single-slice high frequency pulse parameters. In the presentcase, a central excitation frequency, an amplitude scaling factor, and aB1 shimming parameter have been used as single-slice high frequencypulse parameters.

FIG. 4 depicts a further exemplary embodiment, in which the procedurefinds application. In that case, a binomial pulse 12 that is to beapplied to a first slice 1, 2, 3 in turn includes three sub-pulses 13.The last sub-pulse 13 is intended to be emitted superimposed with asingle-slice high frequency pulse 17, such that overall a multi-bandhigh frequency pulse 18 is generated. The sub-pulses 13 and thesingle-slice high frequency pulse 17 for both slices are phase-modulatedand added together in order to obtain the multi-band high frequencypulse 18. It is clear that, in the present exemplary embodiment, thecorrection of the slice selection gradient pulses 14, that is thegradient offset 15, is only applied for as long as only one slice, inthis case the first slice, is affected (sub-section 16). However, assoon as both slices are affected, gradient pulse 14′, in the presentcase no correction is applied; alternatively, an averaged correctionthat is valid for both slices may be used.

It is further pointed out that, in the second exemplary embodiment inFIG. 4, the binomial pulse 12 provides that only water is excited forthe first slice, yet fat and water alike are excited for the secondslice.

In this way, the specific correction of the gradient pulses 14 for thefirst slice, which is affected by the first two sub-pulses 13, is activefor the majority of the water excitation phase, such that thefat-suppression homogeneity shows a clear improvement. The sub-section16 only ends when an overall pulse affecting both slices is emitted.

FIG. 5 finally depicts a sketch illustrating the principle of a magneticresonance apparatus 19. As is basically known, this has a main magnetunit 20, in which a patient recess 21 is embodied, into which a patientmay be taken for imaging as an examination subject 4. Basic knowncomponents of the magnetic resonance apparatus 19, (e.g., a gradientcoil arrangement, a high frequency coil arrangement, a patient couch,and the like), are not shown in greater detail for reasons of clarity.

The operation of the magnetic resonance apparatus 19 is controlled by acontrol device 22, which is also embodied to carry out the method. Forthis purpose, the control device 22 may also include, in addition to atleast one sequence control unit, at least one correction unit todetermine and apply the correction parameters.

It is to be understood that the elements and features recited in theappended claims may be combined in different ways to produce new claimsthat likewise fall within the scope of the present disclosure. Thus,whereas the dependent claims appended below depend from only a singleindependent or dependent claim, it is to be understood that thesedependent claims may, alternatively, be made to depend in thealternative from any preceding or following claim, whether independentor dependent, and that such new combinations are to be understood asforming a part of the present specification.

While the present disclosure has been described above by reference tovarious embodiments, it may be understood that many changes andmodifications may be made to the described embodiments. It is thereforeintended that the foregoing description be regarded as illustrativerather than limiting, and that it be understood that all equivalentsand/or combinations of embodiments are intended to be included in thisdescription.

1. A method for simultaneous recording of magnetic resonance datarelating to an examination subject from at least two different slices bya magnetic resonance sequence, wherein the magnetic resonance sequencecomprises an excitation period, wherein the excitation period includesat least one sub-section that acts on only one slice of the at least twodifferent slices, and wherein the excitation period of the magneticresonance sequence contains at least one high-frequency pulse, themethod comprising: determining, for each slice affected by asub-section, a correction parameter that modifies gradient pulses to beemitted, wherein the determining of the correction parameter takes intoaccount at least one main magnetic field map that describes a spatialdistribution of a main magnetic field and a slice position of theaffected slice; applying the correction parameter in an emission of thegradient pulses for the respective slice in the sub-section to correctmain magnetic field inhomogeneities of a first order; and simultaneouslyrecording the magnetic resonance data from the at least two differentslices by the magnetic resonance sequence.
 2. The method of claim 1,further comprising: determining a gradient offset to be applied to aslice selection gradient as the correction parameter.
 3. The method ofclaim 2, further comprising: determining a correction parameter for eachslice in each remaining section of the excitation period that includehigh frequency pulses and/or sub-pulses acting on a plurality of slicesand applying the correction parameter in each case for all the affectedslices.
 4. The method of claim 1, further comprising: determining acorrection parameter for each slice in each remaining section of theexcitation period that include high frequency pulses and/or sub-pulsesacting on a plurality of slices and applying the respective correctionparameter in each case for all the affected slices.
 5. The method ofclaim 1, wherein, for each slice, single-slice high frequency pulseparameters that describe single-slice pulses of the excitation periodaffecting the respective slice are determined based on the slicepositions and are corrected taking into account the main magnetic fieldmap and/or a high frequency field map that describes the spatialdistribution of the high frequency field and the respective sliceposition, and wherein the high frequency pulses to be emitted in theexcitation period are determined based on the corrected single-slicehigh frequency pulse parameters.
 6. The method of claim 5, wherein acentral excitation frequency, an amplitude scaling factor, a B1-shimmingparameter, or a combination thereof are used as single-slice highfrequency pulse parameters.
 7. The method of claim 1, furthercomprising: emitting, in the sub-section, a pulse sequence serving tosaturate or excite spins of a particular spin type in the affectedslice.
 8. The method of claim 7, wherein the pulse sequence comprises afrequency-selective binomial pulse, a subsequent dephasing gradientpulse, or a combination thereof.
 9. The method of claim 1, wherein atleast one binomial pulse that includes sub-pulses that act on only oneslice is used as a high frequency pulse, and wherein the sub-pulses thatact on only one slice define the sub-section.
 10. A magnetic resonanceapparatus comprising: a control apparatus configured to: determine, foreach slice affected by a sub-section, a correction parameter thatmodifies gradient pulses to be emitted taking into account at least onemain magnetic field map that describes a spatial distribution of a mainmagnetic field and a slice position of each affected slice; apply thecorrection parameter in an emission of the gradient pulses for therespective slice in the sub-section to correct main magnetic fieldinhomogeneities of a first order; and simultaneously record magneticresonance data from at least two different slices by a magneticresonance sequence, wherein an excitation period of the magneticresonance sequence includes the sub-section that acts on only one sliceof the at least two different slices and contains at least onehigh-frequency pulse.
 11. An electronically readable data carriercomprising: at least one computer program configured to cause a magneticresonance apparatus to at least perform: determine, for each sliceaffected by a sub-section, a correction parameter that modifies gradientpulses to be emitted taking into account at least one main magneticfield map that describes a spatial distribution of a main magnetic fieldand a slice position of each affected slice; apply the correctionparameter in an emission of the gradient pulses for the respective slicein the sub-section to correct main magnetic field inhomogeneities of afirst order; and simultaneously record magnetic resonance data from atleast two different slices by a magnetic resonance sequence, wherein anexcitation period of the magnetic resonance sequence includes thesub-section that acts on only one slice of the at least two differentslices and contains at least one high-frequency pulse.